U.S. patent application number 15/483495 was filed with the patent office on 2018-10-11 for optical detection of air bubbles in either saline or blood or a mixture of both.
The applicant listed for this patent is Fresenius Medical Care Holdings, Inc.. Invention is credited to Mohammad M. Khair.
Application Number | 20180289882 15/483495 |
Document ID | / |
Family ID | 63710679 |
Filed Date | 2018-10-11 |
United States Patent
Application |
20180289882 |
Kind Code |
A1 |
Khair; Mohammad M. |
October 11, 2018 |
OPTICAL DETECTION OF AIR BUBBLES IN EITHER SALINE OR BLOOD OR A
MIXTURE OF BOTH
Abstract
Embodiments of the disclosure provide a system and method for
detection of a transient air bubble in an arterial blood flow path
during dialysis (e.g., hemodialysis). The system uses measurements
from an optical sensor to remove one or more effects of common
factors affecting the absorbance of the light incident on the
arterial tubing. These factors include color of medium within the
arterial tubing, tubing color, angle of illumination, and
temperature of the optical detector. A variance of the measurements
from the optical sensor are used to determine whether an air bubble
is present.
Inventors: |
Khair; Mohammad M.; (Irvine,
CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Fresenius Medical Care Holdings, Inc. |
Waltham |
MA |
US |
|
|
Family ID: |
63710679 |
Appl. No.: |
15/483495 |
Filed: |
April 10, 2017 |
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61M 1/3626 20130101;
G01N 33/49 20130101; A61M 2205/3313 20130101 |
International
Class: |
A61M 1/36 20060101
A61M001/36; G01N 21/3577 20060101 G01N021/3577; G01N 21/3504
20060101 G01N021/3504; G01N 33/49 20060101 G01N033/49 |
Claims
1. A method for detecting air bubbles in a blood flow path using at
least one light emitter to generate different wavelengths and at
least one photosensor, the method comprising: setting initial
intensities of light at each wavelength emanating from the at least
one light emitter; determining intensities of light received at the
at least one photosensor, wherein the light received at the at
least one photosensor traverses the blood flow path; determining
one or more normalized ratios using the initial intensities of
light at each wavelength emanating from the at least one light
emitter and the intensities of light at each wavelength received at
the at least one photosensor; and determining whether an air bubble
is present in the blood flow path based on the determined one or
more normalized ratios.
2. The method according to claim 1, further comprising: generating
an alarm and/or stopping a pumping operation in response to
determining that an air bubble is present in the blood flow
path.
3. The method according to claim 1, wherein the at least one light
emitter comprises at least one light emitting diode (LED) and the
at least one photosensor comprises at least one photodiode.
4. The method according to claim 3, wherein setting the initial
intensities of light emanating from the at least one light emitter
comprises: providing at least one electrical current at at least
one predetermined current level to the at least one LED.
5. The method according to claim 3, wherein determining the
intensities of light received at the at least one photosensor
comprises: receiving at least one electrical current from the at
least one photodiode, each electrical current being proportional to
light intensity sensed by a respective photodiode.
6. The method according to claim 3, wherein determining the one or
more normalized ratios comprises: obtaining, for each wavelength,
absorbance of light intensity in the blood flow path, wherein the
absorbance is a difference between the initial intensity of light
emanating from a respective LED and the intensity of light received
at a respective photodiode; and obtaining a normalized ratio by
dividing an absorbance from one wavelength with an absorbance from
another wavelength.
7. The method according to claim 6, wherein: two wavelengths are
generated by the LED, the two wavelengths being a red light
wavelength and an infrared wavelength; and the normalized ratio is
obtained by dividing an absorbance for the red light wavelength by
an absorbance for the infrared wavelength.
8. The method according to claim 1, wherein a sampling rate for
determining whether an air bubble is present in the blood flow path
is within the range of 100 Hz to 1000 Hz.
9. A system for detecting air bubbles in a blood flow path, the
system comprising: at least one light emitter configured to
generate different wavelengths; at least one photosensor; and a
processor, configured to: set initial intensities of light at each
wavelength emanating from the at least one light emitter; determine
intensities of light received at the at least one photosensor,
wherein the light received at the photosensor traverses the blood
flow path; determine one or more normalized ratios using the
initial intensities of light at each wavelength emanating from the
at least one light emitter and the intensities of light at each
wavelength received at the at least one photosensor; and determine
whether an air bubble is present in the blood flow path based on
the determined one or more normalized ratios.
10. The system according to claim 9, wherein the processor is
further configured to: generate an alarm and/or stop a pumping
operation in response to determining that an air bubble is present
in the blood flow path.
11. The system according to claim 9, wherein the at least one light
emitter comprises at least one light emitting diode (LED) and the
at least one photosensor comprises at least one photodiode.
12. The system according to claim 11, further comprising: at least
one LED driver configured to provide electrical current at at least
one predetermined current level to the at least one LED.
13. The system according to claim 11, wherein the processor is
further configured to determine intensities of light received at
the at least one photosensor based on at least one electrical
current generated by the at least one photodiode, each electrical
current being proportional to light intensity sensed by a
respective photodiode.
14. The system according to claim 11, wherein the processor is
further configured to: obtain, for each wavelength, absorbance of
light intensity in the blood flow path, wherein the absorbance is a
difference between the initial intensity of light emanating from a
respective LED and the intensity of light received at a respective
photodiode; and obtain a normalized ratio by dividing an absorbance
from one wavelength with an absorbance from another wavelength.
15. The system according to claim 14, wherein: two wavelengths are
generated by the at least one LED, the two wavelengths being a red
light wavelength and an infrared wavelength; and the normalized
ratio is obtained by dividing an absorbance for the red light
wavelength by an absorbance for the infrared wavelength.
16. The method according to claim 9, wherein a sampling rate for
determining whether an air bubble is present in the blood flow path
is within the range of 100 Hz to 1000 Hz.
17. A non-transitory computer-readable medium having
processor-executable instructions for detecting air bubbles in a
blood flow path using at least one light emitter to generate
different wavelengths and at least one photosensor, the
processor-executable instructions, when executed, facilitating
performance of the following: setting initial intensities of light
at each wavelength emanating from the at least one light emitter;
determining intensities of light received at the at least one
photosensor, wherein the light received at the at least one
photosensor traverses the blood flow path; determining one or more
normalized ratios using the initial intensities of light at each
wavelength emanating from the at least one light emitter and the
intensities of light at each wavelength received at the at least
one photosensor; and determining whether an air bubble is present
in the blood flow path based on the determined one or more
normalized ratios.
18. The non-transitory computer-readable medium according to claim
17, wherein the processor-executable instructions, when executed,
further facilitate: generating an alarm and/or stopping a pumping
operation in response to determining that an air bubble is present
in the blood flow path.
19. The non-transitory computer readable medium according to claim
17, wherein the at least one light emitter comprises at least one
light emitting diode (LED) and the at least one photosensor
comprises at least one photodiode.
20. The non-transitory computer readable medium according to claim
19, wherein determining the one or more normalized ratios
comprises: obtaining, for each wavelength, absorbance of light
intensity in the blood flow path, wherein the absorbance is a
difference between the initial intensity of light emanating from a
respective LED and the intensity of light received at a respective
photodiode; and obtaining a normalized ratio by dividing an
absorbance from one wavelength with an absorbance from another
wavelength.
Description
BACKGROUND
[0001] Patients with kidney failure or partial kidney failure
typically undergo hemodialysis treatment, often at a hemodialysis
treatment center or clinic. When healthy, kidneys maintain the
body's internal equilibrium of water and minerals (e.g., sodium,
potassium, chloride, calcium, phosphorous, magnesium, and sulfate).
The kidneys also function as part of the endocrine system to
produce the hormone erythropoietin as well as other hormones.
Hemodialysis is an imperfect treatment to replace kidney function,
in part, because it does not correct the endocrine functions of the
kidney.
[0002] In hemodialysis, blood is taken from a patient through an
intake needle (or catheter) which draws blood from an artery
located in a specific accepted access location (arm, thigh,
subclavian, etc.). The drawn blood is pumped through extracorporeal
tubing via a peristaltic pump, and then through a dialyzer which
removes unwanted toxins such as blood urea, nitrogen, potassium,
and excess water from the blood. As the blood passes through the
dialyzer, it travels in straw-like tubes which serve as
semi-permeable membrane passageways for the uncleaned blood. Fresh
dialysate liquid, which is a solution of chemicals and water, flows
through the dialyzer in the direction opposite the blood flow. As
the dialysate flows through the dialyzer, it surrounds the
straw-like membranes in the dialyzer. The fresh dialysate collects
excess impurities passing through the straw-like tubes by
diffusion, and also collects excess water through an
ultrafiltration process due to a pressure drop across the
membranes. The used dialysate exits the dialyzer with the excess
fluids and toxins via an output tube, thus cleansing the blood
flowing through the dialyzer. The dialyzed blood then flows out of
the dialyzer via tubing and a needle (or catheter) back into the
patient. Sometimes, a heparin drip or pump is provided along the
extracorporeal blood flow loop in order to prevent clotting during
the hemodialysis process. Several liters of excess fluid can be
removed during a typical multi-hour treatment session. In the U.S.,
a chronic patient will normally undergo hemodialysis treatment in a
dialysis center three times per week, either on
Monday-Wednesday-Friday schedule or a Tuesday-Thursday-Saturday
schedule.
[0003] Hemodialysis has an acute impact on the fluid balance of the
body due in part to the rapid change in circulating blood volume.
When the fluid removal rate is more rapid than the plasma refilling
rate of the body, intravascular blood volume decreases. The
resulting imbalance has been linked to complications such as
hypotension, loss of consciousness, headaches, vomiting, dizziness
and cramps experienced by the patient, both during and after
dialysis treatments. Continuous quantitative measurement of
parameters relating to the circulating blood volume (in real-time)
during hemodialysis reduces the chance of dialysis-induced
hypotension, and otherwise optimizes dialysis therapy regimes by
controlling fluid balance and aiding in achieving the appropriate
dry weight for the patient.
SUMMARY
[0004] One embodiment of the disclosure provides a method for
detecting air bubbles in a blood flow path using at least one light
emitter to generate different wavelengths and at least one
photosensor. The method includes: setting initial intensities of
light at each wavelength emanating from the at least one light
emitter; determining intensities of light received at the at least
one photosensor, wherein the light received at the at least one
photosensor traverses the blood flow path; determining one or more
normalized ratios using the initial intensities of light at each
wavelength emanating from the at least one light emitter and the
intensities of light at each wavelength received at the at least
one photosensor; and determining whether an air bubble is present
in the blood flow path based on the determined one or more
normalized ratios.
[0005] Another embodiment of the disclosure provides a system for
detecting air bubbles in a blood flow path. The system includes: at
least one light emitter configured to generate different
wavelengths; at least one photosensor; and a processor, configured
to: set initial intensities of light at each wavelength emanating
from the at least one light emitter; determine intensities of light
received at the at least one photosensor, wherein the light
received at the photosensor traverses the blood flow path;
determine one or more normalized ratios using the initial
intensities of light at each wavelength emanating from the at least
one light emitter and the intensities of light at each wavelength
received at the at least one photosensor; and determine whether an
air bubble is present in the blood flow path based on the
determined one or more normalized ratios.
[0006] Yet another embodiment of the disclosure provides a
non-transitory computer-readable medium having processor-executable
instructions for detecting air bubbles in a blood flow path using
at least one light emitter to generate different wavelengths and at
least one photosensor. The processor-executable instructions, when
executed, facilitating performance of the following: setting
initial intensities of light at each wavelength emanating from the
at least one light emitter; determining intensities of light
received at the at least one photosensor, wherein the light
received at the at least one photosensor traverses the blood flow
path; determining one or more normalized ratios using the initial
intensities of light at each wavelength emanating from the at least
one light emitter and the intensities of light at each wavelength
received at the at least one photosensor; and determining whether
an air bubble is present in the blood flow path based on the
determined one or more normalized ratios.
BRIEF DESCRIPTION OF THE DRAWINGS
[0007] FIG. 1 is a perspective view of a typical patient undergoing
hemodialysis treatment with a non-invasive, optical blood monitor
monitoring the patient's blood in real-time as it passes through
extracorporeal tubing in the hemodialysis system;
[0008] FIG. 2 illustrates an exemplary system for measuring blood
constituents according to some embodiments of the disclosure;
[0009] FIG. 2A illustrates another exemplary system for measuring
blood constituents according to some embodiments of the
disclosure;
[0010] FIG. 3 illustrates a process of detecting an air bubble
according to some embodiments of the disclosure; and
[0011] FIG. 4 illustrates example waveforms showing absorbance
characteristics and a ratio of the absorbances.
DETAILED DESCRIPTION
[0012] In a renal dialysis treatment session, occlusion of an
arterial blood access line due to blood flow at high flow rates
(300-500 ml/min) may result in very low negative pressures (<200
mmHg) which would result in degassing of the blood. As such, air
bubble detection is important for indicating whether an arterial
occlusion has occurred. One way of optically detecting air bubbles
is with a single light intensity wavelength. The optical air bubble
detection on the arterial line can thus be used for indicating an
arterial occlusion event and alarming a user. While optical air
bubble detection is desirable, and can be achieved with a single
light intensity wavelength, it is affected by several factors
affecting the single light wavelength absorbance.
[0013] Single light wavelength absorbance is affected by the color
of the medium or blood, which varies significantly based on the
blood hematocrit concentration and oxygenation level. Single light
wavelength is also affected by sensor to sensor variability across
multiple sensors. A sensor includes a single wavelength source or
emitter and a single wavelength detector. Sensor to sensor
variability may be reduced through a self-normalization step where
sensor measurements are normalized relative to a baseline of its
measurement. For example, an empty tubing may be used with a sensor
to characterize the sensor's profile while adjusting light input to
the sensor. This self-normalization or sensor calibration can be
performed on each source-detector combination to ensure signal
integrity and sensor response at wavelength of interest.
[0014] Also during dialysis, the disposable tubing that contains
blood and through which the optical detection is taking place
undergoes discoloration and loses some of its transparency over
time, thus affecting measurements relying on single light
wavelength absorbance. Other factors affecting single light
wavelength absorbance include transient effects during dialysis.
For example, when a saline solution dose is introduced and mixes
with blood, the blood becomes diluted the color of the medium
contained in the tubing lightens. Furthermore, when the saline
delivery ends, and blood returns to the tubing mixing with saline
currently in the tubing, the color of the medium contained in the
tubing darkens.
[0015] Saline delivery is typically clinically introduced during
dialysis treatment in order to deliver medications to the patient,
or in the case of a patient suffering from hypovolemia, saline is
introduced to allow for rapid patient recovery. Such variability in
factors affecting the absolute intensity of light absorption makes
the detection of air based purely on intensity level of light of a
single wavelength challenging and difficult to adapt with the
various factors. Using a single wavelength, an optical sensor
typically interprets detection of blood when the single wavelength
light is mostly absorbed (or equivalently reduced transmission of
light), thus resulting in a low-range sensor output. Using a single
wavelength, the presence of air in the tubing produces scattering,
which also reduces transmission, but not as much as blood, and thus
resulting in a mid-range sensor output. Using a single wavelength,
the presence of clear water or saline in the tubing results in
focused transmission with little absorbance of the single
wavelength light, thus resulting in a high-range sensor output. A
single wavelength optical sensor may then be used to obtain
"typical" levels of sensor outputs for blood, air, and saline in
order to interpret contents of the tubing during dialysis.
[0016] Embodiments of the disclosure provide an improved
methodology for detection of a transient air bubble by removing one
or more effects of common mode factors affecting the absorbance of
the light, such as, medium color, tubing color, angle of
illumination, or temperature of the optical detector. In one
embodiment, the methodology involves using a normalized ratio (R)
of the absorbance intensity of two light wavelengths through the
medium. By using the normalized ratio R, common factors affecting
the absolute scale of light intensity are eliminated. Only factors
affecting the wavelengths differently result in a change to the
value and sensitivity of the normalized ratio R. When taking a
ratio, their effects cancel out.
[0017] FIG. 1 is a perspective view of a typical patient undergoing
hemodialysis treatment with a non-invasive, optical blood monitor
monitoring the patient's blood in real-time as it passes through
extracorporeal tubing in the hemodialysis system. The environment
illustrated in FIG. 1 is usable with exemplary embodiments of the
present disclosure. Further, it will be appreciated that the
environment shown in FIG. 1 is merely exemplary, and that the
principles discussed herein with respect to exemplary embodiments
of the present disclosure may be implemented in other environments
as well.
[0018] FIG. 1 illustrates a patient 10 undergoing hemodialysis
treatment using a conventional hemodialysis system 12, as well as a
non-invasive, optical blood monitor 14. A typical hemodialysis
clinic will have several hemodialysis systems 12 for treating
patients on a Monday-Wednesday-Friday schedule or a
Tuesday-Thursday-Saturday schedule. While the invention is not
limited to the number of hemodialysis systems located at a clinic,
or the specific type of hemodialysis system, the general operation
of the hemodialysis system 12 is helpful for understanding the
environment in which the invention is intended to operate.
[0019] An input needle or catheter 16 is inserted into an access
site of the patient 10, such as in the arm, and is connected to
extracorporeal tubing 18 that leads to a peristaltic pump 20 and
then to a dialyzer or blood filter 22. The dialyzer 22 removes
toxins and excess fluid from the patient's blood. The dialyzed
blood is returned from the dialyzer 22 through extracorporeal
tubing 24 and return needle or catheter 26. In some parts of the
world, the extracorporeal blood flow may additionally receive a
heparin drip to prevent clotting. The excess fluids and toxins are
removed by clean dialysate liquid which is supplied to the dialyzer
22 via tube 28 and removed for disposal via tube 30. A typical
hemodialysis treatment session takes about 3 to 5 hours in the
United States.
[0020] In the exemplary environment depicted in FIG. 1, the optical
blood monitor 14 includes a blood chamber 32, an optical blood
sensor assembly 34, and a controller 35. The blood chamber 32 is
preferably located in line with the extracorporeal tubing 18
upstream of the dialyzer 22. Blood from the peristaltic pump 20
flows through the tubing 18 into the blood chamber 32. The
preferred sensor assembly 34 includes LED photo emitters that emit
light at optical wavelengths. The blood chamber 32 includes lenses
so that the emitters and detectors of the sensor assembly 34 can
view the blood flowing through the blood chamber 32, and determine
whether a transient air bubble is detected in the blood.
[0021] In another exemplary environment, the optical blood monitor
includes an optical blood sensor assembly and a controller and does
not include a blood chamber. The optical blood sensor assembly
clasps onto the extracorporeal tubing upstream of the dialyzer. The
blood sensor assembly includes LED photo emitters that emit light
in optical wavelengths including red light, infrared light,
ultraviolet light, blue light, green light, and/or any wavelength
in the optical spectrum. The emitted light travels from the LED
photo emitters through the extracorporeal tubing to light detectors
(e.g. photodiodes) also included in the optical blood sensor
assembly.
[0022] FIG. 2 illustrates an exemplary system 200 that may be used
to measure blood constituents using an optical blood sensor
assembly according to some embodiments of the disclosure. An LED
current driver 202 produces multiple currents to drive an LED array
204. The LED array 204 contains LED1 to LEDN. Each LED in the LED
array 204 operates at a different wavelength, and the LED current
driver 202 is configured to provide power to turn ON or turn OFF
each LED in the LED array 204.
[0023] FIG. 2 shows that processor 216 controls the LED current
driver 202, so in some embodiments, the processor 216 may determine
which LEDs should be turned ON at a certain time during
measurement. Light from the LED array 204 is incident on a blood
container 208, passes through a blood flow path 206, and is
detected at a photosensor 210 (or "photodetector") which may be a
photodiode. The blood container 208 may be, for example, a blood
chamber 32 located in line with an extracorporeal tubing 18, or may
be, for example, the extracorporeal tubing 18 itself. The
photosensor 210 may be one or more photosensors sensitive to
wavelengths emitted by the LED array 204. The photosensor 210
collects and integrates detected LED light and generates a current.
The current is then amplified and filtered by the receiver 212. The
receiver 212 may also convert the amplified and filtered current
from an analog signal to a digital signal, providing the digital
signal to the processor 216 for further analysis.
[0024] The processor 216 is designed to interface with other
electronic components allowing input and output communication of
signals to and from the optical blood sensor assembly. For example,
apart from the blood container 208 including the blood path 206,
every other component identified in system 200 may be part of a
optical blood sensor assembly, for example, an optical blood sensor
assembly 34 as depicted in FIG. 1. Using the embodiment in FIG. 1,
the optical blood sensor assembly 34 may communicate with a
controller 35 for displaying system outputs and/or receiving
command signals or calibration signals.
[0025] In some embodiments, the processor 216 performs calculations
and analyses based on the digital signal received from the receiver
212 and determines whether air bubbles are present in the blood
flow path 206. In other embodiments, the processor 216 may provide
the digital signal received from the receiver 212 to an external
computing device using the input/output communication channels so
that the external computing device, for example, controller 35,
determines whether air bubbles are present in the blood flow path
206. Processor 216 may be a microprocessor, a microcontroller, a
field programmable gate array (FPGA), a complex programmable logic
device (CPLD), an application specific integrated circuit (ASIC),
etc.
[0026] FIG. 2A illustrates another exemplary system 201 that may be
used to measure blood constituents using an optical blood sensor
assembly according to some embodiments of the disclosure. The
system 201 includes a processor 217, LED current driver 203, a
multi-wavelength LED 205, a blood flow path 207, a tubing 209, a
wideband photosensor 211, and a receiver/signal processor 213. The
multi-wavelength LED 205 may generate more than one wavelength, and
the wideband photosensor 211 is sensitive to the more than one
wavelength generated by the multi-wavelength LED 205. The
receiver/signal processor 213 is configured to obtain a current
from the photosensor 211 and separate the magnitude of the current
contributions of the different wavelengths sensed by the wideband
photosensor 211. The receiver/signal processor 213 may separate the
current contributions from the different wavelengths using digital
and/or analog signal processing. The receiver/signal processor 213
then provides the separated current contributions to the processor
217.
[0027] The exemplary systems depicted in FIG. 2 and FIG. 2A may be
used for detection of air bubbles by continuous monitoring of a
blood flow path. The Beer-Lambert law defines the concentration
c.sub.1 of an absorbent in solution to be determined by the
intensity of light transmitted through the solution, knowing the
path length d.sub..lamda., the intensity of the incident light
I.sub.0,.lamda., and the extinction coefficient
.epsilon..sub.i,.lamda. at a particular wavelength .lamda.. In
generalized from, the Beer-Lambert law is expressed as Eq. (1):
I.sub..lamda.=I.sub.0,.lamda..times.e.sup.d.sup..lamda..sup..times..mu..-
sup.a,.lamda. (Eq. 1)
where
.mu..sub.a,.lamda.=.SIGMA..sub.i=1.sup.n.epsilon..sub.i,.lamda..tim-
es.c.sub.i, and where .mu..sub.a,.lamda. is the bulk absorption
coefficient that represents the probability of absorption per unit
length, assuming photon scattering in the solution is
negligible.
[0028] In an exemplary embodiment, the detected absorbance of a
first light wavelength's intensity, called I.sub.A, is divided by
the detected absorbance of a second light wavelength's intensity,
called I.sub.B, thus producing a ratio of R=I.sub.A/I.sub.B, which
represents the normalized ratio R of Beer-Lambert's light intensity
at wavelength A over the Beer-Lambert light intensity at wavelength
B. Note that I.sub.A and I.sub.B represent detected absorbance
parameters. Detected absorbance is defined as light intensity
absorbed by absorbents in the medium or solution as defined in the
Beer-Lambert law. The detected absorbance may be obtained through a
source-detector measurement system by subtracting the light
intensity received at the detector from the light intensity
provided at the source. For example, in FIG. 2, LED 1 in LED array
204 emits 810 nm wavelength light with intensity I.sub.emit,810nm,
and the light travels through the blood flow path 206 and is
incident on one photosensor in photosensor 210. The processor 216
determines the light intensity to be I.sub.detect,810nm. The
detected absorbance I.sub.810nm is determined as
I.sub.emit,810nm-I.sub.detect,810nm.
[0029] The ratio R=I.sub.A/I.sub.B normalizes all common components
affecting the plurality of light wavelengths' absorbance intensity.
The ratio R will therefore be limited in its sensitivity to the
actual factors distinctly affecting the light wavelengths
individually as opposed to common factors affecting all
wavelengths' intensities. Such normalization methods are effective
in limiting the sensitivity of the detection ratios to the
transient factors, such as, air bubble presence.
[0030] During dialysis, the color of the medium in the tubing, for
example, the extracorporeal tubing 18, presents itself as a
persistent value to the absorbance variable that is slowly varying.
For example, the color of the medium when changing from blood to
saline and back to blood will take on a gradual, slowly changing
transient characteristic with an intermediary that is a mixture of
both saline and blood. When air bubbles are present, however, a
rapid variation occurs in the measured absorbance of the medium.
Therefore, in some embodiments, a variance of the measured
absorbance in the blood flow path 206 may be used to detect the
presence of air bubbles. Embodiments of the disclosure thus provide
an ability to avoid false alarms due to gradual changes in color of
the medium (blood or saline or mixture thereof) caused by
slow-varying transitions in the respective concentrations of blood
and saline. Blood tubing color changes are also eliminated since
these color changes are also slowly varying compared to air bubble
presence. As such, the system is more robust and reliable for air
bubble detection for arterial occlusion indication.
[0031] Due to the transient nature of the composition of the
medium, a sampling rate may be defined for the measurement system
of FIGS. 1, 2 and 2A. For example, the optical sensor assembly 34
may make measurements with a sampling rate varying from 100 Hz to
1000 Hz. The sampling rate should be fast enough to realize fast
passing transient bubble events under flowing fluid conditions.
[0032] In an exemplary embodiment, the optical sensor assembly 34
includes an LED that emits light in a red light wavelength, an LED
that emits light in an infrared wavelength, a photosensor sensitive
to red light wavelengths, and a photosensor sensitive to infrared
wavelengths. Since the photosensors are sensitive to specific
wavelength regimes, the LED-photosensor pairs for the red light
wavelength and the infrared wavelength are operated at the same
time to obtain measurements. That is, both LEDs are ON at the same
time, and both photosensors are receptive at the same time to
obtain simultaneous measurements at the red light wavelength and
the infrared wavelength. A normalized ratio can then be determined
based on the measurements.
[0033] FIG. 3 illustrates an exemplary process 300 of detecting an
air bubble according to some embodiments of the disclosure. The
process 300 may be performed, for example, using the optical sensor
assembly 34 in the environment illustrated in FIG. 1. In the setup
of FIG. 1, light sources in the optical sensor assembly 34 are
turned ON. At step 302, the light intensities emanating from light
emitters are determined. Using the illustration in FIG. 2, light
emitters or light sources are the LED array 204. Light intensity of
an LED in the LED array 204 is directly proportional to electrical
current flowing through the LED. The processor 216 controls the LED
current driver 202, which provides electrical current to the LED
array 204, thereby controlling the light intensity of LEDs in the
LED array 204. As such, at step 302, the processor 216 knows the
current provided to an LED by the LED current driver 202 (which
corresponds to the output intensity for the LED). For example, if
two LEDs are in the LED array 204, with a first LED operating in
the red light wavelength and the second LED operating in the
infrared wavelength, the processor 216 determines the current
provided to the first LED (I.sub.emit,A) and the current provided
to the second LED (i.sub.emit,B).
[0034] At step 304, the light intensities detected at the
photosensors are determined. A photosensor may generate a current
proportional to an intensity of light incident upon the
photosensor. For example, in accordance with FIG. 2, two
photosensors are provided: a first photosensor (sensitive to light
in the red light wavelength) and a second photosensor (sensitive to
light in the infrared wavelength). After the light emanating from
each of the first LED and the second LED travels through the blood
flow path 206, the intensity of the light in each wavelength is
changed. The light received at the first photosensor and the second
photosensor causes a current proportional to the light intensity to
be generated at each respective photosensor. Note that the first
photosensor is sensitive to red light wavelength and will generate
current proportional to only red light wavelength received, and the
second photosensor is sensitive to infrared wavelength and will
generate current proportional to infrared wavelength received. The
receiver 212 then processes each current generated by each
photosensor. The receiver 212 may have multiple channels to receive
multiple currents from multiple photosensors detecting light at
different wavelengths. The processor 216 receives from the receiver
212 a value for the current detected at the first photosensor
(i.sub.detect,A) and a value for the current detected at the second
photosensor (I.sub.detect,B).
[0035] At step 306, one or more normalized ratios are determined
from light intensities absorbed in the blood flow path 206. That
is, the normalized ratios are determined using the emanating light
intensities obtained at step 302 and the received light intensities
measured at step 304. For example, in accordance with FIG. 2, the
processor 216 determines a normalized ratio R using i.sub.emit,A,
i.sub.emit,B, i.sub.detect,A, and i.sub.detect,B. Determining the
normalized obtain current differences i.sub.A and i.sub.B,
respectively. The current differences i.sub.A and i.sub.B are
proportional the light intensities of red light wavelength and
infrared wavelength, respectively, that are absorbed in the blood
flow path 206. The normalized ratio R then equals
i.sub.A/i.sub.B.
[0036] At step 308, the processor 216 or a measurement system, for
example, controller 35 determines whether an air bubble is
detected. Step 308 involves comparing historical values of the
normalized ratio R to determine a change in the normalized ratio R.
For example, steps 302, 304, and 306 were performed at a previous
time, and a normalized ratio R.sub.prev was stored in a
non-transitory computer readable medium accessible by the
measurement system. The measurement system then determines the
change in the normalized ratios R and R.sub.prev, normalized ratios
at the current time period and the previous time period,
respectively. If the change from a previous time period to a next
time period meets or exceeds a predetermined threshold, the
measurement system determines that an air bubble is detected. The
system may then take an appropriate action at step 312 in response
to detecting an air bubble, such as generating an alarm or stopping
the pumping operation. The alarm may include, for example, an
auditory alert generated at the controller 35, a visual alert such
as a message or graphic displayed at the controller 35 or some
other measurement system, or other forms of auditory, visual, data
logging, and/or haptic notifications. Additionally or
alternatively, the measurement system may automatically stop a
pump, for example, the peristaltic pump 20 associated with pumping
blood from the patient 10 through the dialyzer 22.
[0037] If the change from the previous time period to the next time
period is below the predetermined threshold, the measurement system
continues monitoring the normalized ratios at step 310 by
performing steps 302, 304, and 306 to obtain a new normalized ratio
for comparison at step 308.
[0038] The detection of an air bubble at step 308 may indicate a
degassing of blood--i.e., that the blood is under extreme negative
pressure. Negative pressure signifies that there is an occlusion or
collapse in the blood flow path, and continuing to pump under these
conditions generates more negative pressure and may cause further
complications. Thus, it is advantageous in certain situations to
stop the pump when an air bubble is detected.
[0039] For example, if an arterial wall collapse causes an air
bubble, stopping the pump gives a caregiver time for the artery
walls to expand before resuming operation at a slower flowrate. In
some cases, the caregiver may gradually increase or ramp up the
flowrate from the slower flowrate to a higher flowrate. Different
patients come with different artery compliances, and attempting to
pull blood from a collapsed artery will not result in blood being
pulled. Thus, embodiments of the disclosure provide a system that
detects when an artery wall collapses and alerts caregivers so they
may reduce the flowrate of the peristaltic pump 20 to match a
patient's artery compliance.
[0040] In another example, if a needle being lodged against the
arterial wall causes an air bubble, stopping the pump gives a
caregiver the chance to adjust the needle and restart the pulling
of blood from the patient. The needle being lodged against the
arterial wall blocks the blood flow path, thus creating negative
pressure that may result in the creation of air bubbles.
[0041] In yet another example, if a kink in tubing causes an air
bubble, stopping the pump gives a caregiver the chance to adjust
the tubing and restart the pulling of blood from the patient.
[0042] Process 300 involves monitoring the rate of change of the
normalized ratio R over time. This may be accomplished using a
predefined sampling rate, for example, a sampling rate between 100
Hz and 1000 Hz. Thus, a normalized ratio R is determined at
specific times, and the receiver 212 can sample the current
generated at the photosensors at the specified sampling rate. In
this configuration, there is no need to turn the LED array 204 ON
and OFF during measurements.
[0043] In another embodiment, more than two wavelengths may be
used. For example, if a third wavelength is introduced, then the
system may obtain further ratios across the three wavelengths,
including, R.sub.1=I.sub.A/I.sub.B, R.sub.2=I.sub.A/I.sub.C,
R.sub.3=I.sub.B/I.sub.C. When more than two ratios are used, medium
absorbance (e.g., absorbance of blood) will be a function of the
multiple ratios. For example, in an embodiment with three ratios
R.sub.1, R.sub.2, and R.sub.3, the medium absorbance may be written
as f(R.sub.1, R.sub.2, R.sub.3). Linear regression methods may be
used to define the characteristic of the function f.
[0044] In the case where three wavelengths are used, absorbances
I.sub.A, I.sub.B, I.sub.C can provide three ratios I.sub.A/I.sub.B,
I.sub.A/I.sub.C or I.sub.B/I.sub.C. The process for detecting an
air bubble using three wavelengths is similar to that for two
wavelengths, except that more permutations of comparisons are
possible. Potential advantages to having more than two wavelengths
include: (1) different ratio results may reveal additional
information, or (2) one ratio's results may be used to confirm
another ratio's results. Also, using more than two wavelengths and
obtaining more than one ratio provides the ability to adjudicate
confusing or mixed results. For example, in the case where three
wavelengths are used, if historical values of R.sub.1 show an air
bubble is present while historical values of R.sub.2 and R.sub.3
show that no air bubble is present, then the measurement system may
not generate an alarm since two ratios out of three indicate no air
bubble. Thus, the use of more than two wavelengths may yield more
robust true positives.
[0045] FIG. 4 illustrates example waveforms showing absorbance
characteristics and a ratio of the absorbances. Absorbance detected
by an infrared sensor is shown compared to absorbance detected by a
red wavelength sensor, and the ratio of the absorbances is obtained
by dividing the absorbance detected by the infrared sensor by that
detected by the red wavelength sensor. The absorbance
characteristics plotted in FIG. 4 are sample measurements that may
be obtained while monitoring a tubing with different transients due
to a change in the medium contained in the tubing. As shown in FIG.
4, as the medium changes, the absorbance characteristics change
accordingly, thus the red wavelength sensor and the infrared sensor
have a similar shape with different amplitudes. The differing
amplitudes suggest that one wavelength is absorbed more by the
medium and tubing properties than the other wavelength.
[0046] The effect of common mode is removed when looking at the
ratio of the absorbances. The ratio of the absorbances is mostly
flat and non-varying compared to each absorbance characteristic
used to determine the ratio. Effects of the color of the medium
within the tubing or slowly varying color of the tubing are
effectively removed when looking at the ratio. Thus, the ratio does
not vary as much when compared to each of the absorbance
characteristics.
[0047] The rate of change of the ratio can be used to detect fast
transients as shown in FIG. 4. Fast transients are indicative of
the presence of an air bubble. By taking the ratio of absorbances,
slowly varying effects are muted, but fast transients will be
captured and will be easily distinguished. Thus, as can be seen in
FIG. 4, the fast transients corresponding to the present of an air
bubble can clearly be seen when looking at the ratio of the
absorbances over time.
[0048] All references, including publications, patent applications,
and patents, cited herein are hereby incorporated by reference to
the same extent as if each reference were individually and
specifically indicated to be incorporated by reference and were set
forth in its entirety herein.
[0049] The use of the terms "a" and "an" and "the" and "at least
one" and similar referents in the context of describing the
invention (especially in the context of the following claims) are
to be construed to cover both the singular and the plural, unless
otherwise indicated herein or clearly contradicted by context. The
use of the term "at least one" followed by a list of one or more
items (for example, "at least one of A and B") is to be construed
to mean one item selected from the listed items (A or B) or any
combination of two or more of the listed items (A and B), unless
otherwise indicated herein or clearly contradicted by context. The
terms "comprising," "having," "including," and "containing" are to
be construed as open-ended terms (i.e., meaning "including, but not
limited to,") unless otherwise noted. Recitation of ranges of
values herein are merely intended to serve as a shorthand method of
referring individually to each separate value falling within the
range, unless otherwise indicated herein, and each separate value
is incorporated into the specification as if it were individually
recited herein. All methods described herein can be performed in
any suitable order unless otherwise indicated herein or otherwise
clearly contradicted by context. The use of any and all examples,
or exemplary language (e.g., "such as") provided herein, is
intended merely to better illuminate the invention and does not
pose a limitation on the scope of the invention unless otherwise
claimed. No language in the specification should be construed as
indicating any non-claimed element as essential to the practice of
the invention.
[0050] Preferred embodiments of this invention are described
herein, including the best mode known to the inventors for carrying
out the invention. Variations of those preferred embodiments may
become apparent to those of ordinary skill in the art upon reading
the foregoing description. The inventors expect skilled artisans to
employ such variations as appropriate, and the inventors intend for
the invention to be practiced otherwise than as specifically
described herein. Accordingly, this invention includes all
modifications and equivalents of the subject matter recited in the
claims appended hereto as permitted by applicable law. Moreover,
any combination of the above-described elements in all possible
variations thereof is encompassed by the invention unless otherwise
indicated herein or otherwise clearly contradicted by context.
* * * * *